|Publication number||US20050154379 A1|
|Application number||US 11/035,694|
|Publication date||Jul 14, 2005|
|Filing date||Jan 14, 2005|
|Priority date||Jan 31, 2003|
|Also published as||US7766904|
|Publication number||035694, 11035694, US 2005/0154379 A1, US 2005/154379 A1, US 20050154379 A1, US 20050154379A1, US 2005154379 A1, US 2005154379A1, US-A1-20050154379, US-A1-2005154379, US2005/0154379A1, US2005/154379A1, US20050154379 A1, US20050154379A1, US2005154379 A1, US2005154379A1|
|Inventors||Michael McGowan, Charles Hurst, Harry Lambert, Christopher Lumpkin|
|Original Assignee||Innovatech Surgical, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (30), Referenced by (26), Classifications (14), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims the benefit of U.S. Provisional Patent Application No. 60/444,060, filed Jan. 31, 2003, the entire disclosure of which is hereby incorporated herein by reference.
The present invention relates generally to laser probes, and more particularly to an adjustable laser probe for effecting laser-induced photocoagulation to treat areas internal to the eye during vitreoretinal surgery.
A vitreoretinal specialist is an ophthalmic surgeon specializing in the diagnosis and treatment of the retina and vitreous. A vitreoretinal surgeon is often called upon to perform a vitrectomy procedure, which typically involves making three stab incisions for access to the posterior segment (back part) of the eye, i.e. the vitreous cavity. One of those incisions (inferio-temporally) is ultimately used for insertion of an infusion cannula, which is used during surgery to introduce fluids to prevent collapse and otherwise maintain integrity of the eye. The other incisions are needed for insertion of specific surgical instruments. Typical incisions in vitreoretinal surgery are slit-like stab incisions approximately 20 gauge (g) in size. A 20 g incision will usually allow an instrument having a 20 g shaft to be inserted into the eye. Size also refers to the diameter of the tubular shaft of the instrument at both the proximal and distal aspects of the inserted portion of the instrument. Instruments that are used in vitreoretinal surgery typically range in size from 18 g to 42 g.
Some surgical techniques involve use of tracer cannulae for the protection of both internal and external surrounding ocular tissues, for repositioning the infusion cannula to access areas of the eye that are difficult to reach, and for more readily inserting surgical instruments into the eye. These cannulae are positioned inside the incision, extending both internally and externally to the eye, and are left in place during the procedure. They act as a conduit, holding the incision open. The most commonly used sizes of tracer cannulae are 19 g, 20 g and 25 g. The “gauge size” refers to the size of the instrument that will pass through the cannula without interference. These cannulae are rigid and do not allow instruments with working ends larger than the diameter size to pass through.
Vitreoretinal surgeons routinely perform laser-induced photocoagulation of the retina. This procedure can be done in both the office treatment room and the operating room. Photocoagulation is accomplished with either an argon (green) or diode (infrared) wavelength laser. In the office setting, this is performed with the use of a “slit lamp,” an illuminating microscope that also allows the application of laser energy when appropriately equipped. During vitreous surgery in the operating room, an endo ocular laser probe is the most commonly used method to deliver the laser energy. The endo ocular laser probe is inserted into the eye and an aiming beam emitted from the probe helps the surgeon to properly position the probe to the desired treatment area. Laser probe types include laser delivery, illuminating and aspirating. Typical laser delivery laser probes may have either fixed straight, or fixed curved configurations.
Both straight and curved probes have distinct benefits and limitations. A straight endoprobe will benefit the surgeon when he needs to apply laser energy straight on, directly to the posterior area of the retina. However, a straight endoprobe's effectiveness is limited when the surgeon needs to apply laser energy to the peripheral areas of the retina. On the other hand, a curved endoprobe will aid the surgeon when laser energy is needed in the peripheral area of the retina, where a straight probe cannot reach. The curved endoprobe is most limited when laser energy is needed in the posterior area of the retina, where a straight probe would be ideal. Additionally, while a straight probe will fit through a straight trocar cannula, a curved probe will not.
In many instances, the surgeon will require the hospital to maintain in inventory both straight and curved laser probes. This results in added cost to the patient and hospital, requires additional shelf space to store both types of probes, and results in more time to complete the vitrectomy.
An adjustable laser probe is being sold by Synergetics, Inc. of St. Charles, Mo. (Model No. 55.26, accessible via http://www.synergeticsusa.com), as shown in
In use, a surgeon advances the button 3 and sheath 8 to straighten the fiber 6 before introduction of the probe 2 into the eye, and prior to removal of the probe 2 from the eye. This allows the probe 2 to pass through an incision in the eye without damaging ocular tissue. Once inside the eye, the surgeon retracts the button 3 and rigid sheath 8 to allow the flexible fiber 6 to return to the curved configuration, which varies up to about 90 degrees.
With such a probe, the surgeon must continually keep a finger positioned on the slidable button since the sheath 8 is movable independent of the probe's handpiece 4. Additionally, the configuration of the probe is dangerous to a patient in that it operates in a manner that may result in damage to the patient's ocular tissue in unexpected circumstances, e.g. during quick withdrawal from the eye as when a patient “startles” under anesthesia. More specifically, a surgeon's reaction to such circumstances often results in retraction of probe 2/handpiece 4 from the eye, and retraction of the button 3 relative to the handpiece. Such retraction of the button 3 results in retraction of the sheath 8 and corresponding exposure of the fiber 6 in the curved tip configuration. Withdrawing the probe from the eye with the fiber in the curved tip configuration will cause ocular tissue to be damaged as the probe is withdrawn. Accordingly, it is disadvantageous and dangerous to require advancement of the button 3 and sheath 8 (in a certain direction) at the time of withdrawal of the probe from the eye (in an opposite direction) in order to prevent damage to ocular tissue. What is needed is an adjustable laser probe providing straight and curved tip configurations while eliminating or reducing such disadvantages.
The present invention provides an endo ocular laser probe capable of functioning as both a straight and a curved laser probe. The probe includes an elongated handpiece and a rigid cannula fixed to the handpiece to prevent relative translational movement therebetween. An optical fiber for delivering laser energy extends through channels in the handpiece and cannula and is supported for translational movement therein. A slidable button is fixed to the optical fiber, via a rigid sleeve that supports the fiber such that the button and optical fiber move together in the same direction during operation. In this manner, the button may be retracted relative to the handpiece to retract the flexible fiber into the rigid cannula, thereby straightening the fiber, or the button may be advanced relative to the handpiece to extend the fiber from the cannula, thereby exposing the fiber and allowing it to curl into the curved tip configuration. Accordingly, retraction of the both the button and the handpiece in the same direction will cause the fiber to be retracted into the cannula and straightened as the tip of the fiber is withdrawn from the eye, thereby preventing possible damage to ocular tissue.
The fiber may be selectively positioned relative to the button to cause the button to act as a visual indicator of the direction in which the fiber will extend from the cannula. The button may be specially configured with an enlarged head portion to enhance grippability and smooth operation of the button.
The present invention provides a laser probe providing adjustability between straight and curved configurations that eliminates disadvantages associated with the prior art. This laser probe improves the surgeon's ability to reach critical areas within the eye, provides for safer and intuitive surgical maneuverability, and allows for quick visual inspection to confirm proper probe orientation, before extension of the fiber to expose a curved tip.
The endo ocular laser probe of the present invention can function as both a straight and a curved laser probe. Referring now to
The optical fiber 20 is a conventional type optical fiber. For example, two and one half (2.50) meters of length of a quartz optical fiber having a 200 micron diameter, including the light transmitting core 20 a, a conventional buffer 20 b and cladding 20 c, has been found suitable (see
Such optical fibers are typically straight or substantially straight when in a relaxed state. The diameter of the fiber may be selected according to the internal diameter of the cannula 16, or as otherwise necessary to be compatible with the desired incision size. The optical fiber 20 is preferably terminated at its proximal end 23 with a suitable connector, such as SMA connector 24, for connection to a laser source device, as shown in
Referring now to
The cannula 16 is rigid and is fixed to the handpiece 12 to prevent relative movement therebetween, as best shown in
Optionally, friction-reducing material, such as Teflon (polytetrafluoroethylene) or polyamide coating or tubing 17, is provided on or within an inner surface of the cannula 16, to reduce friction between the cannula 16 and the fiber 20, etc., and thereby facilitate extension and retraction of the fiber relative to the cannula 16, as best shown in
To provide for the curved tip configuration, the distal end portion 25 of the optical fiber 20 is enclosed in a resiliently deformable flexible tube 21 that has been pre-bent to an angle of about 90 degrees, such that the tube may be straightened, and yet will resiliently return to its pre-bent configuration, as best shown in
The button 22 is fixed to the optical fiber 20 such that movement of the button 22 causes movement of the fiber in a like direction. In the embodiment shown in
The optical fiber 20, or more specifically at least a portion thereof, extends through the channel 14 of the handpiece 12 and into the cannula 16 and is supported for translational movement therein, as best shown in
Referring now to the alternative embodiment of
In an embodiment in which the probe includes a flexible tube 21 providing a curved tip configuration, when the distal end 25 of the optical fiber 20 is assembled within the handpiece 12, the flexible tube 21 protrudes from the cannula 16 to form the desired bend, e.g. a bend ranging from approximately 0° to approximately 90°, with a radius of approximately 0.1 to approximately 0.25 inches.
In a preferred embodiment, the flexible tube 21 is mounted on the optical fiber 20 and/or the optical fiber 20 is positioned relative to the handpiece 12, such that the optical fiber 20 will bend substantially in a central plane of the button 22, e.g. the plane of cross-section of
Accordingly, the probe 10 functions such that when the button 22 is moved distally (advanced), the optical fiber 20 advances and flexes toward its pre-bent curved shape, up to about 90 degrees and in line with the button 22. When the button 22 is moved proximally (retracted), the optical fiber 20 retracts into the non-flexible, stationary cannula 16 attached to the handpiece.
Optionally, the handpiece 12 and the optical fiber's external cladding 19 are made of translucent materials. For example, white Delrin (acetal resin) and white PVC have been found to be suitable for the handpiece and cladding, respectively. This allows for visual inspection of the optical fiber/probe for defects or discontinuities in the optical fiber or inconsistencies in performance when laser source is used that propagates light of a wavelength visible to the human eye. Specifically, such defects or discontinuities will allow escape of some laser light, which will be readily apparent upon visual inspection as a glow at the point of the defect, e.g. a green glow when a green argon laser is used.
Accordingly, the present invention provides a laser probe that does not require the surgeon's finger to remain on the button at all times, as is recommended for prior art probes, and yet the longitudinal position and directional orientation of the distal end of the optical fiber remains satisfactorily stable and/or predictable. Additionally, the inventive laser probe allows for the retraction of the laser fiber by retracting the button, an intuitive movement, followed by retraction of the instrument from the eye.
In a preferred embodiment, the laser probe is therefore adjustable in that it allows for operation in both straight and curved tip configurations, intuitive in that retracting the button retracts the optical fiber, stable in that the stationary sheath alleviates the need for the surgeon to maintain a finger positioned on the slidable button, informative in that it can be configured such that the button position provides a visual or tactile indication of the direction in which the flexible laser fiber will extend, universal in that it can be configured with any suitable connector for attachment to any suitable laser source, versatile in that it can be produced with cannulas of various sized to accommodate 20 g, 25 g or other desired tip sizes, and visually verifiable in that the laser probe and/or fiber cladding can be constructed of a translucent material to allow for inspection for escape of light in order to detect any functionality issues with the probe, such as broken fibers, tissue coagulation on the probe tip, or a faulty laser source device.
Having thus described particular embodiments of the invention, various alterations, modifications, and improvements will readily occur to those skilled in the art. Such alterations, modifications and improvements as are made obvious by this disclosure are intended to be part of this description though not expressly stated herein, and are intended to be within the spirit and scope of the invention. Accordingly, the foregoing description is by way of example only, and not limiting. The invention is limited only as defined in the following claims and equivalents thereto.
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|U.S. Classification||606/4, 606/15|
|International Classification||A61B18/00, A61B18/22, A61B17/00, A61F9/008|
|Cooperative Classification||A61F2009/00874, A61B2018/00196, A61F9/008, A61B18/22, A61F9/00821, A61B2017/00424|
|European Classification||A61F9/008C, A61F9/008|
|Mar 22, 2006||AS||Assignment|
Owner name: INNOVATECH SURGICAL, INC., NEW JERSEY
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MCGOWAN, SR., MICHAEL J.;HURST, JR., CHARLES R.;LAMBERT,M.D., HARRY MICHAEL;AND OTHERS;SIGNING DATES FROM 20050318 TO 20050319;REEL/FRAME:017343/0356
|Jun 8, 2010||AS||Assignment|
Owner name: IRIDEX CORPORATION,CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:INNOVATECH SURGICAL, INC.;REEL/FRAME:024499/0282
Effective date: 20100604
Owner name: IRIDEX CORPORATION, CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:INNOVATECH SURGICAL, INC.;REEL/FRAME:024499/0282
Effective date: 20100604
|Jan 8, 2014||FPAY||Fee payment|
Year of fee payment: 4